US20080309330A1

US20080309330A1 - Magnetic particle imaging apparatus, method of disposing detection coil for magnetic particle imaging apparatus, and magnetic flux detecting apparatus

Info

Publication number: US20080309330A1
Application number: US12/138,132
Authority: US
Inventors: Shigeharu Ohyu; Motoji Haragashira; Yasuo Sakurai
Original assignee: Toshiba Corp; Toshiba Medical Systems Corp
Current assignee: Canon Medical Systems Corp
Priority date: 2007-06-15
Filing date: 2008-06-12
Publication date: 2008-12-18
Also published as: CN101940472B; JP5100212B2; JP2008307254A; US8350566B2; CN101322646B; CN101322646A; CN101940472A

Abstract

In a magnetic particle imaging apparatus that forms an image of a distribution of magnetic particles based on changes in a magnetic flux generated by magnetization of the magnetic particles, modulation coils that magnetize magnetic particles present in a field free area by applying a modulation magnetic field to the field free area, and detection coils are disposed such as to suppress an influence caused by a magnetic flux of the modulation magnetic field applied by the modulation coils and included in a detected magnetic flux.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is based upon and claims the benefit of priority from the prior Japanese Patent Application No. 2007-158546, filed on Jun. 15, 2007; the entire contents of which are incorporated herein by reference.

BACKGROUND OF THE INVENTION

1. Field of the Invention
The present invention relates to a magnetic particle imaging apparatus that forms an image of a distribution of magnetic particles based on change in magnetic flux caused by magnetization of the magnetic particles, a method of disposing a detection coil for the magnetic particle imaging apparatus, and a magnetic flux detecting apparatus. In particular, the present invention relates to a technology for enhancing detection sensitivity of the detection coil.
2. Description of the Related Art
In recent years, a method has been proposed for injecting magnetic particles, such as super paramagnetic iron oxide, that serve as a contrast medium into a subject and forming an image of a distribution of the contrast medium (refer to, for example, JP-A 2003-199767 (KOKAI) or B. Gleich, J. Borgert, J. Weizenecker, “Magnetic Particle Imaging (MPI)”, Philips Medic Mundi Vol. 50 No. 1, 2006/5 [online], May 23, 2007, retrieved from the Internet: URL: http://www.medical.philips.com/main/news/assets/docs/medi camundi/mm_vol50_no1/12_Gleich.pdf). This method is called magnetic particle imaging. FIG. 16 is a diagram for explaining a principle of magnetic particle imaging. In magnetic particle imaging, for example, a static magnetic field 1 flowing in vertically opposite directions is generated using a permanent magnet in an area in which magnetic particles are distributed.
At this time, a magnetic field from above and a magnetic field from below are mutually cancelled at an approximate center of the static magnetic field 1, thereby generating an area 2 where a localized magnetic field becomes zero. The area 2 is referred to as a “field free area”. Then, a modulation coil 4 for generating a modulation magnetic field and a detection coil 5 for detecting a change in an interlinking magnetic flux are disposed within the static magnetic field 1.
Here, it is assumed that a modulation magnetic field 3 is generated in the area in which the magnetic particles are distributed by applying an electrical current to the modulation coil 4. At this time, magnetic saturation occurs in areas other than the field free area 2 because of the static magnetic field 1. Therefore, the magnetic flux within the areas other than the field free area 2 does not change even when the modulation magnetic field 3 is applied. On the other hand, magnetic saturation does not occur in the field free area 2 because the magnetic field is near to zero. When the modulation magnetic field 3 is applied, the magnetic particles present in the field free area 2 become magnetized. A magnetic flux is generated from the field free area 2 with the magnetization of the magnetic particles.
The magnetic flux generated from the field free area 2 causes a change in the magnetic flux interlinked with the detection coil 2. The change in the magnetic flux appears as a change in voltage induced in the detection coil 5. An amount of change in the voltage depends on an amount of magnetic particles present in the field free area 2. In other words, the voltage induced in the detection coil 5 changes based on the amount of magnetic particles present in the field free area 2.
When the above-described principle is used, an image of the distribution of the magnetic particles within the subject can be formed by measuring a change in the voltage induced in the detection coil being measured while the field free area is gradually moved within the subject into which the magnetic particles have been injected. In recent years, a deliberation has begun on clinical application of the above-described magnetic particle imaging.
In the above-described magnetic particle imaging, the change in the voltage induced by the magnetization of the magnetic particles is required to be measured using the detection coil. However, voltage caused by the modulation magnetic field applied by the modulation coil is also induced in the detection coil. The detection coil detects voltage as a modulation signal (such as high-frequency signal). However, when the voltage caused by the modulation magnetic field is also induced, a signal indicating the change in the voltage caused by the magnetization of the magnetic particles and a signal indicating change in the voltage caused by the modulation magnetic field are detected in an overlapping state. Therefore, when an image of the distribution of the magnetic particles is formed, it is required to extract only the signal of the voltage induced by the magnetization of the magnetic particles from the signals detected by the detection coil.
However, the voltage induced by the modulation magnetic field is significantly larger than the voltage induced by the magnetic particles. Therefore, separation of the respective signals of the voltages becomes difficult. This problem becomes more significant in clinical application.
For example, when a magnetic particle imaging apparatus scaled for humans is configured based on a description written in “Magnetic Particle Imaging (MPI)” by B. Gleich, J. Borgert, and J. Weizenecker, and it is assumed that a magnitude of the modulation magnetic field applied by the modulation coil is 10 mT/μ₀, that is a strength facilitating magnetic saturation of the magnetic particles, the voltage induced in the detection coil by the modulation magnetic field is about 150 volts. On the other hand, for example, when an early stage cancer cell of 10 mm³indicating diamagnetism having a magnetic susceptibility of −7.1×10⁻⁶is the subject, the voltage induced in the detection coil is about 50 nanovolts.
A known document describes a separation method using frequency as a method for separating the signals. Specifically, the method takes advantage of the signal of the voltage induced by the magnetization of the magnetic particles including distortion, whereas the signal of the voltage induced by the modulation magnetic field is a sine wave. A harmonic component is extracted from the signals detected by the detection coil. As a result, only the signal of the voltage induced by the magnetization of the magnetic particles is extracted.
However, when taking into consideration of clinical application, because the voltage induced by the modulation magnetic field is significantly larger than the voltage induced by the magnetization of the magnetic particles, as described above, it id difficult to obtain sufficient detection sensitivity even using this method. Therefore, to apply the magnetic particle imaging to a clinical application, the detection sensitivity of the detection coil is required to be significantly enhanced compared to a conventional detection coil.

SUMMARY OF THE INVENTION

According to one aspect of the present invention, a magnetic particle imaging apparatus includes a magnet unit that generates a magnetic field such as to form a non-magnetic field area within a detection space; a modulation coil that magnetizes magnetic particles by applying a modulation magnetic field; a detection coil that detects a change in a magnetic flux interlinked with the detection coil and is disposed such as to suppress an influence caused by a magnetic flux of the modulation magnetic field applied by the modulation coil and included in the detected magnetic flux; and an image processing unit that forms an image of a distribution of the magnetic particles based on the change in the magnetic flux detected by the detection coil.
According to another aspect of the present invention, a method of disposing detection coil for a magnetic particle imaging apparatus, the method includes disposing a modulation coil that magnetizes magnetic particles by applying a modulation magnetic field and a detection coil that detects a change in a magnetic flux interlinked with the detection coil, such that an influence caused by a magnetic flux of the modulation magnetic field applied by the modulation coil and included in the detected magnetic flux is suppressed.
According to still another aspect of the present invention, a magnetic flux detecting apparatus includes a modulation coil that magnetizes magnetic particles by applying a modulation magnetic field; and a detection coil that detects a change in a magnetic flux interlinked with the detection coil, and that is disposed such that an influence caused by a magnetic flux of the modulation magnetic field applied by the modulation coil and included in the detected magnetic flux is suppressed.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of a configuration of a magnetic particle imaging apparatus according to a first embodiment;

FIGS. 2A and 2B are diagrams for explaining permanent magnets;

FIGS. 3A to 3F are diagrams for explaining zero magnetic-field scan coils;

FIGS. 4A and 4B are diagrams explaining modulation coils;

FIGS. 5A to 5C are schematic diagrams indicating waveforms of a magnetic field generated from a field free area;

FIG. 6 is a diagram of an arrangement of detection coil according to the first embodiment;

FIG. 7 is a distribution diagram of distribution of a modulation magnetic field applied by modulation coils;

FIG. 8 is a diagram of an arrangement example of the detection coil shown in FIG. 6;

FIG. 9 is a diagram (1) of another arrangement example of the detection coil;

FIG. 10 is a diagram (2) of another arrangement example of the detection coil;

FIG. 11 is a diagram (3) of another arrangement example of the detection coil;

FIG. 12 is a diagram (4) of another arrangement example of the detection coil;

FIG. 13 is a diagram for explaining control of a feedback coil according to a second embodiment;

FIG. 14 is a diagram of another arrangement example of a feedback coil;

FIG. 15 is a diagram of another example of the configuration of the magnetic particle imaging apparatus; and

FIG. 16 is a diagram for explaining a principle of the magnetic particle imaging apparatus.

DETAILED DESCRIPTION OF THE INVENTION

Exemplary embodiments of a magnetic particle imaging apparatus, a method of disposing a detection coil for the magnetic particle imaging apparatus, and a magnetic flux detecting apparatus according to the present invention are below described with reference to the attached drawings.
FIG. 1 is a perspective view of a configuration of a magnetic particle imaging apparatus according to a first embodiment. As shown in FIG. 1, a magnetic particle imaging apparatus 10 includes a frame 11, a top plate 12, permanent magnets 13 a and 13 b, zero magnetic-field scan coils 14 a to 14 h, modulation coils 15 a and 15 b, detection coils 16 a and 16 b, and an image processing unit 30.
The frame 11 is a u-shaped component and supports the permanent magnets 13 a and 13 b, the zero magnetic-field scan coils 14 a to 14 h, the modulation coils 15 a and 15 b, and the detection coils 16 a and 16 b.
The top plate 12 is a plate-shaped component provided in an approximate center of an area surrounded by the frame 11. A subject P (such as a patient) to be imaged is placed on the top plate 12. The top plate 12 is moved by an apparatus (not shown). Here, directions above and below, right and left, and head and feet are defined based on the subject P placed on the top plate 12 on his back.
The permanent magnets 13 a and 13 b are magnets used to generate a field free area within the frame 11. FIGS. 2A and 2B are diagrams for explaining the permanent magnets 13 a and 13 b. As shown in FIG. 2A, the permanent magnets 13 a and 13 b are respectively disposed on an upper surface and a lower surface of an inner wall of the frame 11. The permanent magnets 13 a and 13 b are disposed facing each other.
The permanent magnets 13 a and 13 b are disposed such that respectively generated magnetic fields flow in opposite directions. As a result of the permanent magnets 13 a and 13 b being disposed in this way, as shown in FIG. 2 b, a magnetic field 6 a generated by the permanent magnet 13 a and a magnetic field 6 b generated by the permanent magnet 13 b are mutually cancelled at the middle point of the permanent magnet 13 a and 13 b, thereby generating a field free area 2.
Here, as shown in the diagrams, a surface passing through a center of the field free area 2 and dividing the area surrounded by the frame 11 into left and right is referred to as a “horizontal center surface”. A surface passing through the center of the field free area 2 and dividing the area surrounded by the frame 11 into top and bottom is referred to as a “vertical center surface”.
The zero magnetic-field scan coils 14 a to 14 h are electromagnets used to control a position of the field free area 2. FIGS. 3A to 3F are diagrams for explaining the zero magnetic-field scan coils 14 a to 14 h. FIG. 3A shows a state of a magnetic field on the vertical center surface shown in FIG. 2B. As shown in FIG. 3A, on the vertical center surface, a magnetic field 6 c is generated that is a combination of the magnetic field 6 a and the magnetic field 6 b shown in FIG. 2B. The field free area 2 is generated in a center portion of the magnetic field 6 c.
FIG. 3B shows the top plate 12, the permanent magnet 13 a disposed on an upper surface of the inner wall of the frame 11, and the zero magnetic-field scan coils 14 a to 14 d. As shown in FIG. 3B, the zero magnetic-field scan coils 14 a to 14 d are disposed around the permanent magnet 13 a.
Specifically, a zero magnetic-field scan coil 14 a is disposed on a right side of a head end from the perspective of the subject P. A zero magnetic-field scan coil 14 b is disposed on a left side of the head end. A zero magnetic-field scan coil 14 c is disposed on the right side of a feet end. A zero magnetic-field scan coil 14 d is disposed on the left side of the feet end.
For example, it is assumed that electric current flowing through each zero magnetic-field scan coil is adjusted such that a magnetic field flowing from the zero magnetic-field scan coil 14 b towards the zero magnetic-field scan coil 14 a and a magnetic field flowing from the zero magnetic-field scan coil 14 d towards the zero magnetic-field scan coil 14 c are generated. In this case, as shown in FIG. 3C, a magnetic field flowing from the left side to the right side is generated. When the generated magnetic field and the magnetic field 6 c shown in FIG. 3A are combined, the combined magnetic field on the right side becomes stronger than the combined magnetic field on the left side. As a result, as shown in FIG. 3D, the field free area 2 moves to the left side. On the other hand, when the electrical current is adjusted such that a magnetic field flowing from the zero magnetic-field scan coil 14 a towards the zero magnetic-field scan coil 14 b and a magnetic field flowing from the zero magnetic-field scan coil 14 c towards the zero magnetic-field scan coil 14 d are generated, the field free area 2 moves to the right side.
At the same time, for example, it is assumed that the current flowing through each coil is adjusted such that a magnetic field flowing from the zero magnetic-field scan coil 14 c towards the zero magnetic-field scan coil 14 a and a magnetic field flowing from the zero magnetic-field scan coil 14 d towards the zero magnetic-field scan coil 14 b are generated. In this case, as shown in FIG. 3E, a magnetic field flowing from the feet end to the head end is generated. When the generated magnetic field and the magnetic field 6 c shown in FIG. 3A are combined, the combined magnetic field on the feet end becomes stronger than the combined magnetic field on the head end. As a result, as shown in FIG. 3F, the field free area 2 moves to the feet end. On the other hand, when the electrical current is adjusted such that a magnetic field flowing from the zero magnetic-field scan coil 14 a towards the zero magnetic-field scan coil 14 c and a magnetic field flowing from the zero magnetic-field scan coil 14 b towards the zero magnetic-field scan coil 14 d are generated, the field free area 2 moves to the head end.
In this way, the field free area 2 can be moved in the horizontal direction and the head and feet direction by the electrical currents flowing through the zero magnetic-field scan coils 14 a to 14 d being respectively adjusted. Although explanations are omitted herein, the field free area 2 can be similarly moved when the zero magnetic-field scan coils 14 e to 14 h disposed on the lower surface of the inner wall of the frame 11 are used.
In the configuration of the zero magnetic-field scan coils 14 a to 14 h, described above, the field free area 2 cannot be moved vertically. However, the position of the field free area 2 can be equivalently moved within the subject P by the top plate 12 being moved in the vertical direction.
The modulation coils 15 a and 15 b are coils that magnetize magnetic particles by applying a modulation magnetic field. Specifically, the modulation coils 15 a and 15 b are electromagnets used to apply a modulation magnetic field in the area surrounded by the frame 11. The modulation coils 15 a and 15 b apply a modulation magnetic field of, for example, about 10 kilohertz to 100 kilohertz. FIGS. 4A and 4B are diagrams for explaining the modulation coils 15 a and 15 b. As shown in FIG. 4A, the modulation coils 15 a and 15 b are respectively disposed on an upper side and a lower side of the area surrounded by the frame 11. The modulation coils 15 a and 15 b are disposed facing each other. The modulation coils 15 a and 15 b apply the modulation magnetic field 3 from the lower side towards the upper side.
When the modulation coils 15 a and 15 b apply the modulation magnetic field 3, the magnetic particles present within the field free area 2 are magnetized and magnetization M occurs, as shown in FIG. 4B. A magnetic field 7 is thus generated from the field free area 2 with the magnetization of the magnetic particles. A waveform of the magnetic field 7 is the same as a waveform of the magnetization M. The waveform includes distortion depending on an amount of magnetic particles present within the field free area 2.
FIGS. 5A to 5C are schematic diagrams of a waveform of the magnetic field generated from the field free area 2. FIG. 5A is a schematic diagram of an intensity H of the magnetic field at the field free area 2. FIG. 5B is a schematic diagram of change in magnetic flux density B at the field free area 2. FIG. 5C is a schematic diagram of change in the magnetization M at the field free area 2.
The intensity H of the magnetic field generated near the field free area 2 is a sum of an intensity of the magnetic field generated by the permanent magnets 13 a and 13 b and the intensity of the modulation magnetic field generated by the modulation coils 15 a and 15 b. However, because the magnetic field generated by the permanent magnets 13 a and 13 b at the field free area 2 is zero, the waveform of the intensity H of the magnetic field is a sine wave, as shown in FIG. 5A. At the same time, the magnetic flux density B reaches a plateau at a predetermined saturated magnetic flux density as shown in FIG. 5B, as a result of magnetic saturation. Therefore, the magnetization M has a distorted waveform as shown in FIG. 5C because the magnetization M is a difference between B and μ₀.
The detection coils 16 a and 16 b are electromagnets used to detect an interlinking magnetic flux. When the detection coils 16 a and 16 b are disposed in arbitrary positions within the area surrounded by the frame 11, the magnetic flux detected by the detection coils 16 a and 16 b includes, not only the magnetic flux of the magnetic field 7 generated by the magnetization M of the magnetic particles, but the magnetic flux of the magnetic fields 6 a and 6 b generated by the permanent magnets 13 a and 13 b and the magnetic flux of the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b.
However, only the magnetic flux of the magnetic field 7 generated by the magnetization M of the magnetic particles is required to form an image of the distribution of the magnetic particles. The magnetic fields 6 a and 6 b generated by the permanent magnets 13 a and 13 b are both static magnetic fields. Therefore, frequencies of the magnetic fields 6 a and 6 b significantly differ from the magnetic field 7 generated by the magnetization M. As a result, the magnetic flux of the magnetic fields 6 a and 6 b and the magnetic flux of the magnetic field 7 can be easily separated by a known technology.
On the other hand, when taking into consideration clinical application, the modulation magnetic field 3 generated by the modulation coils 15 a and 15 b is, as described earlier, significantly larger than the magnetic field 7 generated by the magnetization M of the magnetic particles, as described above. Therefore, separation of these magnetic fields is difficult.
Therefore, in the magnetic particle imaging apparatus 10 according to the first embodiment, the detection coils 16 a and 16 b are disposed such that detection of the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b is kept to a minimum (zero in terms of design) and the magnetic field 7 generated by the magnetization M of the magnetic particles can be efficiently detected. As a result, sufficient detection sensitivity can be achieved even in clinical application.
An arrangement of the detection coils 16 a and 16 b will be described in detail hereafter. FIG. 6 is a diagram of an arrangement of the detection coils 16 a and 16 b according to the first embodiment. As shown in FIG. 6, in the magnetic particle imaging apparatus 10 according to the first embodiment, the detection coil 16 a is disposed on an upper right side of the area surrounded by the frame 11. The detection coil 16 b is disposed on the lower right side. Both detection coils 16 a and 16 b are disposed on outer sides of the modulation coils 15 a and 15 b.
Here, the detection coil 16 a is disposed such that mutual inductance with the modulation coil 15 a becomes substantially zero. The detection coil 16 b is disposed such that mutual inductance with the modulation coil 15 b becomes substantially zero.
Specifically, according to the first embodiment, the detection coil 16 a is disposed such that an axis (center axis) running through a center of a coil surface of the detection coil 16 a is approximately orthogonal to the magnetic flux of the modulation magnetic field 3 applied by the modulation coil 15 a to make mutual inductance between the detection coil 16 a and the modulation coil 15 a substantially zero. The detection coil 16 b is disposed such that an axis (center axis) running through a center of a coil surface of the detection coil 16 b is approximately orthogonal to the magnetic flux of the modulation magnetic field 3 applied by the modulation coil 15 b to make mutual inductance between the detection coil 16 b and the modulation coil 15 b substantially zero.
Because the detection coils 16 a and 16 b are disposed as described above, the magnetic flux of the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b is not interlinked with the detection coils 16 a and 16 b. As a result, an influence on the detection coils 16 a and 16 b by the magnetic flux of the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b is restrained.
At the same time, the center axis of each detection coil 16 a and 16 b is not approximately orthogonal to the magnetic flux of the magnetic field 7 generated by the magnetization M of the magnetic particles (which means that the coil surface of each detection coil 16 a and 16 b approximately orthogonal to the magnetic flux of the magnetic field 7). Therefore, the detection coils 16 a and 16 b have a very low detection sensitivity to the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b, and have a certain amount of detection sensitivity to the magnetic field 7 generated by the magnetization M of the magnetic particles.
A method of disposing the detection coils 16 a and 16 b will be described hereafter. Specifically, first, a predetermined number of points are defined within the area surrounded by the frame 11. The points are referred to as “measurement points”. Next, the intensity and direction of the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b are calculated at each measurement point. FIG. 7 is a distribution diagram of a distribution of the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b. A direction of each straight line shown in FIG. 7 indicates the direction of the modulation magnetic field 3 at each measurement point. A length of each straight line indicates an intensity of the modulation magnetic field 3 at each measurement point.
Then, any one of measurement points is selected from among the defined measurement points. The detection coil is disposed so that the center point of the detection coil overlaps with the selected measurement point and the center axis of the detection coil is approximately orthogonal to the direction of the modulation magnetic field 3 at the selected measurement point.
FIG. 8 is a diagram of an arrangement example of the detection coils 16 a and 16 b shown in FIG. 6. For example, as shown in FIG. 8, a measurement point is selected from the upper side and from the lower side, among the measurement points on the right side of the area surrounded by the frame 11 and the outer sides of the modulation coils 15 a and 15 b. The detection coils 16 a and 16 b are disposed based on each measurement point.
The detection coils 16 a and 16 b are disposed in this way such that the center axis of the detection coil is approximately orthogonal to the magnetic flux of the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b. As a result, the magnetic flux detected by the detection coils 16 a and 16 b, among the magnetic flux of the modulation magnetic field 3 generated by the modulation coils 15 a and 15 b, can be suppressed to a minimum.
In above example, detection coil is located approximately orthogonal to the magnetic flux of the modulation magnetic field 3. To explain it more generally, the arrangement of detection coils are made so that the mutual inductance of detection coils and modulation coils are suppressed to a minimum.
Returning to FIG. 1, the image processing unit 30 generates an image indicating the distribution of the magnetic particles based on the change in the magnetic flux detected by the detection coils 16 a and 16 b. The image processing unit 30 outputs the generated image to, for example, a display device such as a monitor and an output device such as a printer.
As described above, according to the first embodiment, the detection coils 16 a and 16 b that detect the change in the interlinking magnetic flux are disposed such as to suppress the influence of the magnetic flux of the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b and included in the detected magnetic flux. Therefore, the detection sensitivity of the detection coil can be enhanced. Sufficient sensitivity can be achieved for clinical application.
According to the first embodiment, when the detection coils 16 a and 16 b are disposed such that the center axes are approximately orthogonal to the direction of the modulation magnetic field 3 generated by the modulation coils 15 a and 15 b is described. However, the present invention is not limited thereto. Various other detection coil disposal methods can be considered. Hereafter, other examples of the detection coil disposal will be described with reference to FIG. 9 to FIG. 12.
FIG. 9 is a diagram (1) of another arrangement example of the detection coil. For example, the detection coils can be disposed on inner sides of the modulation coils 15 a and 15 b. In the example, four detection coils 16 c to 16 f are each disposed based on measurement points on the inner sides of the modulation coils 15 a and 15 b.
Signal detection sensitivity can be further enhanced when the detection coils 16 c to 16 f are disposed on the inner sides of the modulation coils 15 a and 15 b, because each detection coil is disposed closer to the magnetization M than when the detection coils 16 c to 16 f are disposed on the outer sides.
With reference to the distribution diagram in FIG. 7, it is understood that a measurement point is present at which the magnetic field becomes zero as a result of the modulation magnetic field 3 applied by the modulation coil 15 a and the modulation magnetic field 3 applied by the modulation coil 15 b being mutually cancelled. As a result of the detection coils 16 c to 16 f being disposed as described above, the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b and interlinked with the detection coils 16 c to 16 f can become zero.
FIG. 10 is a diagram (2) of another arrangement example of the detection coil. For example, as shown in FIG. 10, a detection coil 16 g is disposed in a position at which the modulation magnetic field 3 generated on the right side of the modulation coil 15 a and the modulation magnetic field 3 generated on the right side of the modulation coil 15 b are mutually cancelled. In this case, regardless of the direction in which the detection coil 16 g is disposed, the modulation magnetic field 3 interlinked with the detection coil 16 g become zero. However, to efficiently detect the magnetic flux of the magnetic field 7 generated by the magnetization M of the magnetic particles, the detection coil 16 g is preferably disposed in a direction in which a coil surface is perpendicular to the magnetic flux of the magnetic field 7. The magnetic flux of the magnetic field 7 interlinked with the detection coil reaches maximum when the detection coil 16 g is disposed in this way. Therefore, the detection sensitivity to the magnetic field 7 of the detection coil also reaches maximum.
Alternatively, the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b can be made zero through use of two serially connected detection coils wound in opposite directions.
FIG. 11 is a diagram (3) of another arrangement example of the detection coil. For example, as shown in FIG. 11, serially connected detection coils 16 h and 16 i wound in opposite directions are respectively disposed above and below the modulation coil 15 a. Here, each detection coil has a same coil surface area and a same number of windings. Each detection coil is disposed at a same distance from the modulation coil 15 a such that the center axis of each detection coil matches the center axis of the modulation coil 15 a.
As a result of the detection coils 16 h and 16 i being disposed in this way, the modulation magnetic fields 3 applied by the modulation coils 15 a and 15 b and detected by each detection coil are mutually cancelled. Therefore, when the detection coils 16 h and 16 i are considered to be a single detection coil, the modulation magnetic field 3 interlinked with the entire detection coil can be considered to be zero.
On the other hand, regarding the magnetic field 7 generated by the magnetization M, because the detection coil 16 i is disposed closer to the field free area 2 than the detection coil 16 h, the magnitude of the interlinking magnet field differs for each detection coil. As a result, even when the detection coils 16 h and 16 i are considered to be a single detection coil, the magnetic field 7 interlinked with the entire detection coil is not zero. Therefore, a difference occurs in the magnetic field 7 interlinked with each detection coil. By detecting the difference, the magnetic field 7 generated by the magnetization M can be detected.
Here, the detection coils 16 h and 16 i have the same coil surface area and the same number of windings. Each detection coil is disposed at a same distance from the modulation coil 15 a such that the center axis of each detection coil matches the center axis of the modulation coil 15 a. However, the coil surface area, the number of windings, and the disposal positions are not limited thereto.
In other words, even when each detection coil is disposed in a position that is a different distance from the modulation coil 15 a, the modulation magnetic field 3 interlinking the entire detection coil can be made zero by the coil surface areas and the number of windings being changed such that the modulation magnetic fields 3 interlinked with each detection coil are mutually cancelled. At this time, each detection coil is preferably disposed such that a total of the magnetic field 7 generated by the magnetization M is as large as possible.
Alternatively, compensation coils can be serially inserted into each modulation coil and detection coil and disposed such as to face each other. As a result, the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b can become zero.
FIG. 12 is a diagram (4) of another arrangement example of the detection coil. For example, as shown in FIG. 12, compensation coils 17 a and 17 b are inserted in a series with the modulation coil 15 a. The compensation coil 17 a is inserted in a series with a detection coil 16 j. At this time, the compensation coils 17 a and 17 b are disposed such as to face each other. A ratio of the number of windings between the compensation coils 17 a and 17 b are set such that a sum of a magnetic flux interlinked with the detection coil 16 j among the magnetic flux of the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b and a magnetic flux interlinked with the compensation coil 17 b and generated by the compensation coil 17 a becomes zero.
The method using the compensation coils as in the example in FIG. 12 is useful for making fine adjustments to make a total amount of the magnetic flux of the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b, among the magnetic flux detected by the detection coil, zero. The method is effective when used in combination with each of the above-described examples.
According to the first embodiment, when the interlinking magnetic flux, among the magnetic flux of the modulation magnetic field 3 applied by the modulation coils 15 a and 15 b, is minimized through adjustment of the position and the direction when the detection coil is disposed is described. However, even when a design is achieved such as to dispose the detection coil as described above, mechanical error may occur during manufacture. Therefore, it is difficult for the magnetic field interlinking with the detection coil and generated by the modulation coils 15 a and 15 b to be made completely zero.
Therefore, according to a second embodiment, following configuration and method are described. In the configuration and method, a feedback coil is provided for adjusting a balance in the modulation magnetic field applied by the modulation coils 15 a and 15 b. The feedback coil is driven based on a result actually detected by the detection coil. As a result, the magnetic field interlinked with the detection coil and generated by the modulation coils 15 a and 15 b is made completely zero. Here, for convenience of explanation, functional sections achieving same purposes as each section in FIG. 1 are given the same reference numbers. Detailed explanations thereof are omitted.
FIG. 13 is a diagram for explaining control of the feedback coil according to the second embodiment. Four serially connected detection coils 16 k to 16 n are disposed, in which two detection coils 16 k and 16 l on the inner side of the modulation coil 15 a and two detection coils 16 m and 16 n on the outer side of the modulation coil 15 b. A feedback coil 18 a is disposed in an approximate center of the modulation coil 15 b.
Here, the modulation coils 15 a and 15 b are driven by a modulation signal supplied by an alternating current power supply 19 b, via an amplifier circuit 19 a. The modulation signal is generally almost a sine wave. However, the modulation signal actually includes some harmonic components for ON/OFF control of the signal, pulse drive, and the like.
A signal detected by the detection coils 16 k to 16 n is inputted into a detection circuit 19 d, via the amplifier circuit 19 c. The detection circuit 19 d performs wave detection on the inputted signal using a signal waveform of the electrical current flowing through the modulation coils 15 a and 15 b. As a result, a basic frequency element is extracted from the inputted signal. A signal of the basic frequency element extracted by the detection circuit 19 d is inputted into an integration circuit 19 e.
The integration circuit 19 e integrates inputted signals and inputs an integration result into a gain adjusting circuit 19 g, via an amplifier circuit 19 f. The gain adjusting circuit 19 g generates a modulation signal of a same frequency waveform as the modulation signal driving the modulation coils 15 a and 15 b, using the integration result as gain. Based on the generated modulation signal, the modulation signal is supplied to the feedback coil 18 a, via an amplifier circuit 19 h.
The above described circuit configuration configures a primary delay system. The primary delay system performs control such that an element with a same frequency as those of the modulation coils 15 a and 15 b, among the magnetic flux interlinked with the detection coils 16 k to 16 n, becomes zero. In the configuration, even when a mechanical error occurs, the magnetic field generated by the feedback coil 18 a is controlled such as to cancel the mechanical error. Therefore, a measurement signal from the detection coil of the modulation magnetic field generated by the modulation coils can be made zero. At the same time, the harmonic component included in the magnetic field generated by the magnetization M remains without being cancelled. Therefore, signal detection accuracy does not deteriorate.
As described above, according to the second embodiment, the modulation coils 15 a and 15 b are driven using the modulation signal waveform. The element synchronous with the modulation signal waveform is extracted from the signal detected by the detection coil. The feedback coil 18 a is controlled such that the synchronous element becomes zero. Therefore, the signal detected by the detection coil within the modulation magnetic field generated by the modulation coils 15 a and 15 b can be significantly reduced, and the detection sensitivity of the detection coil can be further enhanced.
According to the second embodiment, when the feedback coil 18 a is provided in the approximate center of the modulation coil 15 b is described. However, the present invention is not limited thereto. For example, a compensation coil can be connected to the detection coil. The feedback coil can be disposed such as to face the compensation coil. FIG. 14 is another arrangement example of feedback coil.
Specifically, for example as shown in FIG. 14, a compensation coil 17 c is inserted between the detection coils 16 k to 16 n and an amplifier circuit 19 c. A feedback coil 18 b is disposed such as to face the compensation coil 17 c. A modulation signal generated by the gain adjusting circuit 19 g and having a same waveform as the modulation signal driving the modulation coils 15 a and 15 b is supplied to the feedback coil 18 b.
As a result, a magnetic flux canceling the error is generated from the feedback coil 18 b. Control is performed such that the element with the same frequency as those of the modulation coils 15 a and 15 b, among the magnetic flux interlinked with the detection coils 16 k to 16 n, becomes zero.
Alternatively, the modulation signal generated by the gain adjusting circuit 19 g can be directly applied to one of either the modulation coil 15 a or the modulation coil 15 b. The magnetic flux canceling the error is generated from the modulation coil to which the modulation signal is applied. Control is performed such that the element with the same frequency as those of the modulation coils 15 a and 15 b, among the magnetic flux interlinked with the detection coils 16 k to 16 n, becomes zero.
The present invention according to the first embodiment and the second embodiment has been described above. According to these embodiments, the modulation coils 15 a and 15 b are described in which the detection coils are disposed near the permanent magnets 13 a and 13 b. However, the present invention can be similarly applied when the modulation coils have a different configuration.
FIG. 15 is another example of the configuration of the magnetic particle imaging apparatus. In a magnetic particle imaging apparatus 20, a modulation coil 25 and detection coils 26 a to 26 d are each disposed on the top plate 12. A three-dimensional scan is performed during image scanning by the top plate 12 being gradually moved upwards and downwards. Moreover, the top plate 12 can be moved in a head direction and a feet direction.
The modulation coil 25 and the detection coils 26 a to 26 d move with the movement of the top plate 12. Therefore, each coil is constantly disposed close to the subject P, thereby further enhancing the detection sensitivity.
In this case, same as the first embodiment, various patterns can be considered regarding positions and directions when the detection coils are disposed. For example, in the example in FIG. 15, the detection coils 26 a to 26 d are disposed in the same positions as the detection coils 16 d to 16 f in FIG. 9.
As can be analogized by the examples above, the present invention can be similarly applied with various modulation coil and detection coil configurations.
As described above, in the magnetic particle imaging apparatus according to the present invention, the detection coil does not detect the magnetic flux generated by the modulation coil. The detection coil can efficiently extract and detect the magnetic field generated from an area to be imaged. Therefore, the detection sensitivity is significantly enhanced. In a conventional configuration, actualization of an imaging device for humans has been considered difficult. However, through use of the present invention, sensitivity can be significantly enhanced. An imaging apparatus that can be applied to clinical situations can be actualized.
In the conventional configuration of the imaging apparatus, highly concentrated magnetic particles are used. A lesion can be detected only when the lesion becomes very large. However, through use of the present invention, detection can be performed even when concentration of the magnetic particles on an affected area is less than that in the conventional configuration. In addition, magnetic particles concentrated in a small area (affected area) can be detected. Therefore, milder diseases and diseases at an earlier stage can be detected, thereby contributing to improvement in diagnostic quality.
The present invention has been achieved to solve the above described problems and issues of the above described conventional technologies. An object of the invention is to provide a magnetic particle imaging apparatus, a signal detecting method, and a signal detecting apparatus for the magnetic particle imaging apparatus that can be applied to a clinical situation through enhancement of detection sensitivity of a detection coil.
Additional advantages and modifications will readily occur to those skilled in the art. Therefore, the invention in its broader aspects is not limited to the specific details and representative embodiments shown and described herein. Accordingly, various modifications may be made without departing from the spirit or scope of the general inventive concept as defined by the appended claims and their equivalents.

Claims

1. A magnetic particle imaging apparatus comprising:

a magnet unit that generates a magnetic field such as to form a non-magnetic field area within a detection space;

a modulation coil that magnetizes magnetic particles by applying a modulation magnetic field;

a detection coil that detects a change in a magnetic flux interlinked with the detection coil and is disposed such as to suppress an influence caused by a magnetic flux of the modulation magnetic field applied by the modulation coil and included in the detected magnetic flux; and

an image processing unit that forms an image of a distribution of the magnetic particles based on the change in the magnetic flux detected by the detection coil.

2. The apparatus according to claim 1 further comprising a feedback coil that applies a magnetic field for adjusting a magnitude of the magnetic flux of the modulation magnetic field applied by the modulation coil, based on the magnetic flux of the modulation magnetic field included in the magnetic flux detected by the detection coil.

3. The apparatus according to claim 2, wherein

the detection coil has a compensation coil serially connected to the detection coil; and

the feedback coil adjusts the magnitude of the magnetic flux of the modulation magnetic field by applying a magnetic field to the compensation coil of the detection coil.

4. The apparatus according to claim 1, wherein the detection coil is disposed such that mutual inductance with the modulation coil becomes substantially zero.

5. The apparatus according to claim 4 further comprising a feedback coil that applies a magnetic field for adjusting a magnitude of the magnetic flux of the modulation magnetic field applied by the modulation coil, based on the magnetic flux of the modulation magnetic field included in the magnetic flux detected by the detection coil.

6. The apparatus according to claim 5, wherein

7. The apparatus according to claim 1, wherein the detection coil is disposed such that a center axis of the detection coil is approximately orthogonal to the magnetic flux of the modulation magnetic field applied by the modulation coil.

8. The apparatus according to claim 7 further comprising a feedback coil that applies a magnetic field for adjusting a magnitude of the magnetic flux of the modulation magnetic field applied by the modulation coil, based on the magnetic flux of the modulation magnetic field included in the magnetic flux detected by the detection coil.

9. The apparatus according to claim 8, wherein

10. The apparatus according to claim 1, wherein the detection coil is disposed on an outer side of the modulation coil.

11. The apparatus according to claim 1, wherein the detection coil is disposed on an inner side of the modulation coil.

12. The apparatus according to claim 1, wherein

the modulation coil includes at least two coils; and

the detection coil is disposed in a position at which modulation magnetic fields applied by each coil forming the modulation coil are mutually cancelled.

13. The apparatus according to claim 12, wherein the detection coil is disposed such that a coil surface of the detection coil is approximately orthogonal to the magnetic flux generated by magnetization of magnetic particles present in the non-magnetic field area.

14. The apparatus according to claim 1, wherein the detection coil includes at least two serially connected coils, in which each coil is disposed such that the magnetic flux of the modulation magnetic fields included in the detected magnetic flux are mutually cancelled.

15. The apparatus according to claim 1, wherein

the detection coil includes a first compensation coil serially connected to the detection coil; and

the modulation coil includes a second compensation coil that is serially connected to the modulation coil and applies a magnetic field to the first compensation coil such that the magnetic flux of the modulation magnetic fields included in the magnetic flux detected by the detection coil are mutually cancelled.

16. A method of disposing detection coil for a magnetic particle imaging apparatus, the method comprising:

disposing a modulation coil that magnetizes magnetic particles by applying a modulation magnetic field and a detection coil that detects a change in a magnetic flux interlinked with the detection coil, such that an influence caused by a magnetic flux of the modulation magnetic field applied by the modulation coil and included in the detected magnetic flux is suppressed.

17. The method according to claim 16, wherein the detection coil is disposed such that mutual inductance with the modulation coil becomes substantially zero.

18. The method according to claim 16, wherein the detection coil is disposed such that a center axis of the detection coil is approximately orthogonal to the magnetic flux of the modulation magnetic field applied by the modulation coil.

19. The method according to claim 16, wherein

the modulation coil includes at least two coils; and

20. The method according to claim 19, wherein the detection coil is disposed such that a coil surface of the detection coil is approximately orthogonal to the magnetic flux generated by magnetization of magnetic particles present in the non-magnetic field area.

21. A magnetic flux detecting apparatus comprising:

a modulation coil that magnetizes magnetic particles by applying a modulation magnetic field; and

a detection coil that detects a change in a magnetic flux interlinked with the detection coil, and that is disposed such that an influence caused by a magnetic flux of the modulation magnetic field applied by the modulation coil and included in the detected magnetic flux is suppressed.

22. The apparatus according to claim 21, wherein the detection coil is disposed such that mutual inductance with the modulation coil becomes substantially zero.

23. The apparatus according to claim 21, wherein the detection coil is disposed such that a center axis of the detection coil is approximately orthogonal to the magnetic flux of the modulation magnetic field applied by the modulation coil.

24. The apparatus according to claim 21, wherein

the modulation coil includes at least two coils; and

25. The apparatus according to claim 24, wherein the detection coil is disposed such that a coil surface of the detection coil is approximately orthogonal to the magnetic flux generated by magnetization of magnetic particles present in the non-magnetic field area.